Multi-modal compton and single photon emission computed tomography medical imaging system

ABSTRACT

A multi-modality imaging system allows for selectable photoelectric effect and/or Compton effect detection. The camera or detector is a module with a catcher detector. Depending on the use or design, a scatter detector and/or a coded physical aperture are positioned in front of the catcher detector relative to the patient space. For low energies, emissions passing through the scatter detector continue through the coded aperture to be detected by the catcher detector using the photoelectric effect. Alternatively, the scatter detector is not provided. For higher energies, some emissions scatter at the scatter detector, and resulting emissions from the scattering pass by or through the coded aperture to be detected at the catcher detector for detection using the Compton effect. Alternatively, the coded aperture is not provided. The same module may be used to detect using both the photoelectric and Compton effects where both the scatter detector and coded aperture are provided with the catcher detector. Multiple modules may be positioned together to form a larger camera, or a module is used alone. By using modules, any number of modules may be used to fit with a multi-modality imaging system. One or more such modules may be added to another imaging system (e.g., CT or MR) for a multi-modality imaging system.

RELATED CASE

This application is a continuation of U.S. application Ser. No.17/250,543, filed Feb. 2, 2021, which is a 371(c) nationalization ofPCT/US2018/045466, filed Aug. 7, 2018, which are hereby incorporated byreference in their entirety.

BACKGROUND

The present embodiments relate to nuclear imaging, such as single photonemission computed tomography (SPECT) imaging. Slowly rotating largefield-of-view SPECT systems rely on the existence of a physicalcollimator. A parallel-hole collimator, which combined with aposition-sensitive detector, forms the image. Relying on a photoelectriceffect for detecting emissions from a radioisotope in the patient, thesecollimated SPECT systems are limited to low-energy photon emittingisotopes, such as Tc99m. Image quality and efficiency are key parametersof any image formation system for SPECT medical applications. Increasedsensitivity and image quality are desirable features in new SPECT imageformation systems as well as the added possibility of imaging higherphoton energies.

The Compton effect allows for imaging higher energies. Compton imagingsystems are constructed as test platforms, such as assembling a scatterring and then a catcher ring mounted to a large framework. Electronicsare connected to detect Compton-based events from emissions of aphantom. Compton imaging systems have failed to address design andconstraint requirements for practical use in any commercial clinicalsettings. Current proposals lack the ability to be integrated intoimaging platforms in the clinic or lack the design and constraintrequirements (i.e., flexibility and scalability) to address commercialneeds.

SUMMARY

By way of introduction, the preferred embodiments described belowinclude methods and systems for medical imaging. A multi-modalityimaging system allows for selectable photoelectric effect and/or Comptoneffect detection. The camera or detector is a module with a catcherdetector. Depending on the use or design, a scatter detector and/or acoded physical aperture are positioned in front of the catcher detectorrelative to the patient space. For low energies, emissions passingthrough the scatter detector continue through the coded aperture to bedetected by the catcher detector using the photoelectric effect.Alternatively, the scatter detector is not provided. For higherenergies, some emissions scatter at the scatter detector, and resultingemissions from the scattering pass by or through the coded aperture tobe detected at the catcher detector for detection using the Comptoneffect. Alternatively, the coded aperture is not provided. The samemodule may be used to detect using both the photoelectric and Comptoneffects where both the scatter detector and coded aperture are providedwith the catcher detector. Multiple modules may be positioned togetherto form a larger camera or a module is used alone. By using modules, anynumber of modules may be used to fit with a multi-modality imagingsystem. One or more such modules may be added to another imaging system(e.g., CT or MR) for a multi-modality imaging system.

In a first aspect, multi-modality medical imaging system includes afirst module having a first catcher detector, a position for a firstscatter detector spaced from the catcher detector, and a position for afirst physical aperture between a patient space and the first catcherdetector. An image processor is configured to determine angles ofincidence for Compton events where the first scatter detector isincluded in the first module and to count photoelectric events where thefirst physical aperture is included in the first module.

In a second aspect, a medical imaging system includes solid-statedetector modules each with a first detector arranged to be used witheither or both of a plate forming a coded aperture and a scatterdetector. The solid-state detector modules having three, five, or sixsides in a cross-section normal to a radial from longitudinal patientaxis such that the solid-state detector modules stack together to formpart of a geodesic dome.

In a third aspect, a method is provided for forming a Compton cameraand/or a single photon emission computed tomography camera. A catcherdetector is housed in a housing. The catcher detector arranged to beusable for relatively lower emission energies with a coded aperture andto be usable for relatively higher emission energies with a scatterdetector. The housing is shaped as a part of a geodesic dome. Thehousing is mounted relative to a patient bed with a selected one or bothof the coded aperture and the scatter detector.

The present invention is defined by the following claims, and nothing inthis section should be taken as a limitation on those claims. Furtheraspects and advantages of the invention are discussed below inconjunction with the preferred embodiments and may be later claimedindependently or in combination.

BRIEF DESCRIPTION OF THE DRAWINGS

The components and the figures are not necessarily to scale, emphasisinstead being placed upon illustrating the principles of the invention.Moreover, in the figures, like reference numerals designatecorresponding parts throughout the different views.

FIG. 1 is perspective view of multiple modules of a Compton cameraaccording to one embodiment;

FIG. 2 illustrates an example scatter detector;

FIG. 3 illustrates an example catcher detector;

FIG. 4A is a side view of one embodiment of a Compton camera, FIG. 4B isan end view of the Compton camera of FIG. 4A, and FIG. 4C is a detailview of a part of the Compton camera of FIG. 4B;

FIG. 5 is a perspective view of one embodiment of a Compton camera in amedical imaging system;

FIG. 6 is a perspective view of one embodiment of a full-ring Comptoncamera in a medical imaging system;

FIG. 7 is a perspective view of one embodiment of a partial-ring Comptoncamera in a medical imaging system;

FIG. 8 is a perspective view of one embodiment of a full-ring Comptoncamera with partial-rings in axial extension in a medical imagingsystem;

FIG. 9 is a perspective view of one embodiment of a single module-basedCompton camera in a medical imaging system;

FIG. 10 is a flow chart diagram of an example embodiment of a method forforming a Compton camera;

FIG. 11 illustrates the scatter and catcher detectors with anintervening coded aperture for imaging using both photoelectric andCompton effects;

FIG. 12 is a perspective view of one embodiment of a full-ringmulti-modality camera from modules shaped for a geodesic dome-likestructure;

FIG. 13 is a perspective view of one embodiment of a dual-ringmulti-modality camera from modules shaped for a geodesic dome-likestructure;

FIG. 14 is a perspective view of one embodiment of multiple full-ringsstacked axially in a multi-modality camera from modules shaped for ageodesic dome-like structure;

FIG. 15 is a perspective view of one embodiment of a multi-modalitycamera formed from three modules shaped for a geodesic dome-likestructure; and

FIG. 16 is a perspective view of one embodiment of a photoelectriceffect camera formed from three modules shaped for a geodesic dome-likestructure.

DETAILED DESCRIPTION OF THE DRAWINGS AND PRESENTLY PREFERRED EMBODIMENTS

FIGS. 1-9 are directed to a multi-modality compatible Compton camera. Amodular design is used to form the Compton camera for use with variousother imaging modalities. FIGS. 11-16 are directed to a modular designwith a catcher detector that may be used with either a scatter detectorfor Compton imaging or a coded aperture for SPECT imaging. The moduleprovides positions for either or both of the scatter detector and codedaperture. After a summary of the selectable SPECT-Compton embodiments,the Compton camera of FIGS. 1-9 is described. Many of the features andcomponents of the Compton camera of FIGS. 1-9 are used in theSPECT-Compton embodiments described in FIGS. 11-16.

For the selectable SPECT-Compton embodiments, a clinical multi-modalitycompatible and modular camera is provided for medical imaging. For lowerenergy emissions, a coded aperture may be included in each module forSPECT operation. For higher energy emissions, a scatter detector may beincluded in each module for Compton operation The modular design allowsenough flexibility that the selectable SPECT-Compton camera may be addedto existing computed tomography (CT), magnetic resonance (MR), orpositron emission tomography (PET) platforms, either as axiallyseparated systems, or as fully integrated systems. Modularity allowsefficient manufacturing and serviceability. Increased sensitivity andimage quality are desirable features in new SPECT image formationsystems as well as the added possibility of imaging higher photonenergies. Hybrid imaging uses the Compton effect for higher energies andthe photoelectric effect with physical collimation for low energies˜140.5 keV where both the scatter detector and coded aperture areprovided in the respective positions of a same module.

Referring to FIGS. 1-9, a medical imaging system includes amulti-modality compatible Compton camera with segmented detectionmodules. The Compton camera, such as a Compton camera ring, is segmentedinto modules that house the detection units. Each module is independent,and when assembled into a ring or partial ring, the modules maycommunicate with each other. The modules are independent yet can beassembled into a multi-module unit that produces Comptonscattering-based images. Cylindrically symmetric modules or sphericalshell segmented modules may be used.

The scatter-catcher pair, modular arrangement allows efficientmanufacturing, is serviceable in the field, and is cost and energyefficient. The modules allow for the design freedom to change the radiusfor each radial detection unit, angular span of one module, and/or axialspan. The scatter-catcher pair modules are multi-modality compatibleand/or form a modular ring Compton camera for clinical emission imaging.This design allows flexibility, so the Compton camera may be added toexisting computed tomography (CT), magnetic resonance (MR), positronemission tomography (PET) or other medical imaging platforms, either asaxially separated systems or as fully integrated systems. Each modulemay address heat dissipation, data collection, calibration, and/or allowfor efficient assembly as well as servicing.

Each scatter-catcher paired module is formed from commercially suitablesolid-state detector modules (e.g., Si, CZT, CdTe, HPGe or similar),allowing for an energy range of 100-3000 keV. Compton imaging may beprovided with a wider range of isotope energies (>2 MeV), enabling newtracers/markers through selection of the scatter-catcher detectors. Themodularity allows for individual module removal or replacement, allowingfor time and cost-efficient service. The modules may be operatedindependently and isolated or may be linked for cross-talk, allowing forimproved image quality and higher efficiency in detecting Compton eventsusing a scatter detector of one module and a catcher detector of anothermodule.

The modularity allows for flexible design geometry optimized toindividual requirements, such as using a partial ring for integrationwith a CT system (e.g., connected between the x-ray source anddetector), a few modules (e.g., tiling) used for integration with asingle photon emission computed tomography gamma camera or other spacelimited imaging system, or a full ring. Functional imaging based onCompton-detected events may be added to other imaging systems (e.g., CT,MR, or PET). Multiple full or partial rings may be placed adjacent toeach other for greater axial coverage of the Compton camera. A dedicatedor stand-alone Compton-based imaging system may be formed. In oneembodiment, the modules include a collimator for lower energies (e.g.,<300 keV), providing for multichannel and multiplexed imaging (e.g.,high energies using the scatter-catcher detectors for Compton events andlow energies using one of the detectors for SPECT or PET imaging). Themodules may be stationary or fast rotating (0.1 rpm<<ω<<240 rpm). Thedimensional, installation, service, and/or cost constraints areaddressed by the scatter-catcher paired modules.

FIG. 1 shows one embodiment of modules 11 for a Compton camera. Fourmodules 11 are shown, but additional or fewer modules may be used. TheCompton camera is formed from one or more modules, depending on thedesired design of the Compton camera.

The Compton camera is for medical imaging. A space for a patientrelative to the modules is provided so that the modules are positionedto detect photons emitted from the patient. A radiopharmaceutical in thepatient includes a radio-isotope. A photon is emitted from the patientdue to decay from the radio-isotope. The energy from the radio-isotopemay be 100-3000 keV, depending on the material and structure of thedetectors. Any of various radio-isotopes may be used for imaging apatient.

Each of the modules 11 includes the same or many of the same components.A scatter detector 12, a catcher detector 13, circuit boards 14, andbaffle 15 are provided in a same housing 21. Additional, different, orfewer components may be provided. For example, the scatter detector 12and catcher detector 13 are provided in the housing 21 without othercomponents. As another example, a fiber optic data line 16 is providedin all or a sub-set of the modules 11.

The modules 11 are shaped for being stacked together. The modules 11mate with each other, such as having matching indentation andextensions, latches, tongue-and-grooves, or clips. In other embodiments,flat or other surfaces are provided for resting against each other or adivider. Latches, clips, bolts, tongue-and-groove or other attachmentmechanisms for attaching a module 11 to any adjacent modules 11 areprovided. In other embodiments, the module 11 attaches to a gantry orother framework with or without direct connection to any adjacentmodules 11.

The connection or connections to the other modules 11 or gantry may bereleasable. The module 11 is connected and may be disconnected. Theconnection may be releasable, allowing removal of one module 11 or agroup of modules 11 without removing all modules 11.

For forming a Compton camera from more than one module 11, the housing21 and/or outer shape of the modules 11 is wedge shaped. The modules 11may be stacked around an axis to form a ring or partial ring due to thewedge shape. The part closer to the axis has a width size that isnarrower along a dimension perpendicular to the axis than a width sizeof a part further from the axis. In the modules 11 of FIG. 1, thehousings 21 have the widest part furthest from the axis. In otherembodiments, the widest part is closer to the axis but spaced away fromthe narrowest part closest to the axis. In the wedge shape, the scatterdetector 12 is nearer to the narrower part of the wedge shape than thecatcher detector 13. This wedge shape in cross-section along a planenormal to the axis allows stacking of the modules 11 in abuttingpositions, adjacently, and/or connected to form at least part of a ringabout the axis.

The taper of the wedge provides for a number N of modules 11 to form acomplete ring around the axis. Any number N may be used, such as N=10-30modules. The number N may be configurable, such as using differenthousings 21 for different numbers N. The number of modules 11 used for agiven Compton camera may vary, depending on the design of the Comptoncamera (e.g., partial ring). The wedge shape may be provided along otherdimensions, such as having a wedge shape in a cross-section parallel tothe axis.

The modules 11 as stacked are cylindrically symmetric as connected witha gantry of a medical imaging system. A narrowest end of the wedgedcross-section is closest to a patient space of the medical imagingsystem and a widest end of the wedged cross-section may be furthest fromthe patient space. In alternative embodiments, other shapes than wedgeallowing for stacking together to provide a ring or generally curvedshape of the stack may be provided.

The housing 21 is metal, plastic, fiberglass, carbon (e.g., carbonfiber), and/or other material. In one embodiment, different parts of thehousing 21 are of different materials. For example, tin is used for thehousing around the circuit boards 14. Aluminum is used to hold thescatter detector 12 and/or catcher detector 13. In another example, thehousing 12 is of the same material, such as aluminum.

The housing 21 may be formed from different structures, such as endplates having the wedge shape, sheets of ground plane housing thecircuit boards 14, and separate structure for walls holding the scatterdetector 12 and catcher detector 13 where the separate structure isformed of material through which photons of a desired energy from aCompton event may pass (e.g., aluminum or carbon fiber). In alternativeembodiments, walls are not provided for the modules 11 between the endplates for a region where the scatter detector 12 and/or catcherdetector 13 are positioned, avoiding interference of photons passingfrom the scatter detector 12 of one module 11 to a catcher detector 13of another module 11. The housing 21 by and/or for holding the detectors12, 13 is made of low attenuating material, such as aluminum or carbonfiber.

The housing 21 may seal the module or includes openings. For example,openings for air flow are provided, such as at a top of widest portionof the wedge shape at the circuit boards 14. The housing 21 may includeholes, grooves, tongues, latches, clips, stand-offs, bumpers, or otherstructures for mounting, mating, and/or stacking.

Each of the solid-state detector modules 11 includes both scatter andcatcher detectors 12, 13 of a Compton sensor. By stacking each module,the size of the Compton sensor is increased. A given module 11 itselfmay be a Compton sensor since both the scatter detector 12 and catcherdetector 13 are included in the module.

The modules 11 may be separately removed and/or added to the Comptonsensor. For a given module 11, the scatter detector 12 and/or catcherdetector 13 may be removable from the module 11. For example, a module11 is removed for service. A faulty one or both detectors 12, 13 areremoved from the module 11 for replacement. Once replaced, therefurbished module 11 is placed back in the medical imaging system.Bolts, clips, latches, tongue-and-groove, or other releasable connectorsmay connect the detectors 12, 13 or part of the housing 21 for thedetectors 12, 13 to the rest of the module 11.

The scatter detector 12 is a solid-state detector. Any material may beused, such as Si, CZT, CdTe, HPGe, and/or other material. The scatterdetector 12 is created with wafer fabrication at any thickness, such asabout 4 mm for CZT. Any size may be used, such as about 5×5 cm. FIG. 2shows a square shape for the scatter detector 12. Other shapes thansquare may be used, such as rectangular. For the modules 11 of FIG. 1,the scatter detector 12 may be rectangular extending between twowedge-shaped end-plates.

In the module 11, the scatter detector 12 has any extent. For example,the scatter detector 12 extends from one wedge-shaped end wall to theother wedge-shaped end wall. Lesser or greater extent may be provided,such as extending between mountings within the module 11 or extendingaxially beyond one or both end-walls. In one embodiment, the scatterdetector 12 is at, on, or by one end wall without extended to anotherend wall.

The scatter detector 12 forms an array of sensors. For example, the 5×5cm scatter detector 12 of FIG. 2 is a 21×21 pixel array with a pixelpitch of about 2.2 mm. Other numbers of pixels, pixel pitch, and/or sizeof arrays may be used.

The scatter detector 12 includes semiconductor formatted for processing.For example, the scatter detector 12 includes an application specificintegrated circuit (ASIC) for sensing photon interaction with anelectron in the scatter detector 12. The ASIC is collocated with thepixels of the scatter detector 12. The ASIC is of any thickness. Aplurality of ASICs may be provided, such as 9 ASICS in a 3×3 grid of thescatter detector 12.

The scatter detector 12 may operate at any count rate, such as >100kcps/mm. Electricity is generated by a pixel due to the interaction.This electricity is sensed by the application specific integratedcircuit. The location, time, and/or energy is sensed. The sensed signalmay be conditioned, such as amplified, and sent to one or more of thecircuit boards 14. A flexible circuit, wires, or other communicationspath carries the signals from the ASIC to the circuit board 14.

Compton sensing operates without collimation. Instead, a fixedrelationship between energy, position, and angle of a photon interactionat the scatter detector 12 relative to a photon interaction at thecatcher detector 13 is used to determine the angle of the photonentering the scatter detector 12. A Compton process is applied using thescatter detector 12 and the catcher detector 13.

The catcher detector 13 is a solid-state detector. Any material may beused, such as Si, CZT, CdTe, HPGe, and/or other material. The catcherdetector 13 is created with wafer fabrication at any thickness, such asabout 10 mm for CZT. Any size may be used, such as about 5×5 cm. Thesize may be larger along at least one dimension than the scatterdetector 12 due to the wedge shape and spaced apart positions of thescatter detector 12 and the catcher detector 13. FIG. 3 shows arectangular shape for the catcher detector 13 but other shapes may beused. For the modules 11 of FIG. 1, the catcher detector 13 may berectangular extending between two end-plates where the length is thesame as and the width is greater than the scatter detector 12.

The catcher detector 12 forms an array of sensors. For example, the 5×6cm catcher detector 13 of FIG. 3 is a 14×18 pixel array with a pixelpitch of about 3.4 mm. The pixel size is larger than the pixel size ofthe scatter detector 12. The number of pixels is less than the number ofpixels of the scatter detector 12. Other numbers of pixels, pixel pitch,and/or size of arrays may be used. Other relative pixels sizes and/ornumbers of pixels may be used.

In the module 11, the catcher detector 13 has any extent. For example,the catcher detector 13 extends from one wedge-shaped end wall to theother wedge-shaped end wall. Lesser or greater extent may be provided,such as extending between mountings within the module 11 or extendingaxially beyond one or both end-walls. In one embodiment, the catcherdetector 13 is at, on, or by one end wall without extending to anotherend wall.

The catcher detector 13 includes semiconductor formatted for processing.For example, the catcher detector 13 includes an ASIC for sensing photoninteraction with an electron in the catcher detector 13. The ASIC iscollocated with the pixels of the catcher detector 13. The ASIC is ofany thickness. A plurality of ASICS may be provided, such as 6 ASICS ina 2×3 grid of the catcher detector 13.

The catcher detector 13 may operate at any count rate, such as >100kcps/mm. Electricity is generated by a pixel due to the interaction.This electricity is sensed by the ASIC. The location, time, and/orenergy is sensed. The sensed signal may be conditioned, such asamplified, and sent to one or more of the circuit boards 14. A flexiblecircuit, wires, or other communications path carries the signals fromthe ASIC to the circuit board 14.

The catcher detector 13 is spaced from the scatter detector 12 by anydistance along a radial line from the axis or normal to the parallelscatter and catcher detectors 12, 13. In one embodiment, the separationis about 20 cm, but greater or lesser separation may be provided. Thespace between the catcher detector 13 and the scatter detector 12 isfilled with air, other gas, and/or other material with low attenuationfor photons at the desired energies.

The circuit boards 14 are printed circuit boards, but flexible circuitsor other materials may be used. Any number of circuit boards 14 for eachmodule may be used. For example, one circuit board 14 is provided forthe scatter detector 12 and another circuit board 14 is provided for thecatcher detector 13.

The circuit boards 14 are within the housing 21 but may extend beyondthe housing 21. The housing 21 may be grounded, acting as a ground planefor the circuit boards 14. The circuit boards 14 are mounted in parallelwith each other or are non-parallel, such as spreading apart inaccordance with the wedge shape. The circuit boards are positionedgenerally orthogonal to the catcher detector 13. Generally is used toaccount for any spread due to the wedge shape. Brackets, bolts, screws,and/or stand-offs from each other and/or the housing 21 are used to holdthe circuit boards 14 in place.

The circuit boards 14 connect to the ASICS of the scatter and catcherdetectors 12, 13 through flexible circuits or wires. The ASICs outputdetected signals. The circuit boards 14 are acquisition electronics,which process the detected signals to provide parameters to the Comptonprocessor 19. Any parameterization of the detected signals may be used.In one embodiment, the energy, arrival time, and position inthree-dimensions is output. Other acquisition processing may beprovided.

The circuit boards 14 output to each other, such as through a galvanicconnection within a module 11, to the data bridge 17, and/or to a fiberoptic data link 16. The fiber data link 16 is a fiber optic interfacefor converting electrical signals to optical signals. A fiber opticcable or cables provide the acquisition parameters for events detectedby the scatter and catcher detectors 12, 13 to the Compton processor 19.

The data bridge 17 is a circuit board, wires, flexible circuit, and/orother material for galvanic connection to allow communications betweenmodules 11. A housing or protective plate may cover the data bridge 17.The data bridge 17 releasably connects to one or more modules 11. Forexample, plugs or mated connectors of the data bridge 17 mate withcorresponding plugs or mated connectors on the housing 21 and/or circuitboards 14. A latch, clip, tongue-and-groove, screw, and/or boltconnection may be used to releasably hold the data bridge 17 in placewith the modules 11.

The data bridge 17 allows communications between the modules. Forexample, the fiber data link 16 is provided in one modules 11 and notanother module 11. The cost of a fiber data link 16 in every module 11is avoided. Instead, the parameters output by the other module 11 areprovided via the data bridge 17 to the module 11 with the fiber datalink 16. The circuit board or boards 14 of the module 11 with the fiberdata link 16 route the parameter output to the fiber data link 16, usingthe fiber data link 16 to report detected events from more than onemodule 11. In alternative embodiments, each module 11 includes a fiberdata link 16, so the data bridge 17 is not provided or communicatesother information.

The data bridge 17 may connect other signals between the modules 11. Forexample, the data bridge 17 includes a conductor for power.Alternatively, a different bridge provides power to the modules 11 orthe modules 11 are individually powered. As another example, clockand/or synchronization signals are communicated between modules 11 usingthe data bridge 17.

In the embodiment of FIG. 1, a separate clock and/or synchronizationbridge 18 is provided. The clock and/or synchronization bridge 18 is acircuit board, wires, flexible circuit, and/or other material forgalvanic connection to allow communication of clock and/orsynchronization signals between modules 11. A housing or protectiveplate may cover the clock and/or synchronization bridge 18. The clockand/or synchronization bridge 18 releasably connects to one or moremodules 11. For example, plugs or mated connectors of the clock and/orsynchronization bridge 18 mate with corresponding plugs or matedconnectors on the housing 21 and/or circuit boards 14. A latch, clip,tongue-and-groove, screw, and/or bolt connection may be used toreleasably hold the clock and/or synchronization bridge 18 in place withthe modules 11.

The clock and/or synchronization bridge 18 may connect with the same ordifferent grouping of modules 11 as the data bridge 17. In theembodiment shown in FIG. 1, the data bridge 17 connects between pairs ofmodules 11 and the clock and/or synchronization bridge 18 connects overgroups of four modules 11.

The clock and/or synchronization bridge 18 provides a common clocksignal and/or synchronization signals for synchronizing clocks of themodules 11. One of the parameters formed by the circuit boards 14 ofeach module 11 is the time of detection of the event. Compton detectionrelies on pairs of events—a scatter event and a catcher event. Timing isused to pair events from the different detectors 12, 13. The commonclocking and/or synchronization allows for accurate pairing where thepair of events are detected in different modules 11. In alternativeembodiments, only scatter and catcher events detected in a same module11 are used, so the clock and/or synchronization bridge 18 may not beprovided.

Other links or bridges between different modules 11 may be provided.Since the bridges 17, 18 are removable, individual modules 11 may beremoved for service while leaving remaining modules 11 in the gantry.

Each module 11 is air cooled. Holes may be provided for forcing airthrough the module 11 (i.e., entry and exit holes). One or more baffles15 may be provided to guide the air within the module 11. Water,conductive transfer, and/or other cooling may be alternatively oradditionally provided.

In one embodiment, the top portion of the wedge-shape module 11 orhousing 21 is open (i.e., no cover on the side furthest from the patientarea). One or more baffles 15 are provided along the centers of one ormore circuit boards 14 and/or the housing 21. A fan and heat exchanger20 force cooled or ambient temperature air into each module 11, such asalong one half of the module 11 at a location spaced away from thecatcher detector 13 (e.g., top of the module 11). The baffles 15 and/orcircuit boards 14 guide at least some of the air to the airspace betweenthe scatter detector 12 and the catcher detector 13. The air then passesby the baffles 15 and/or circuit boards 14 on another part (e.g.,another half) of the module 11 for exiting to the heat exchanger 20.Other routing of the air may be provided.

The heat exchanger and fan 20 is provided for each individual module 11,so may be entirely or partly within the module 11. In other embodiments,ducting, baffles, or other structure route air to multiple modules 11.For example, groups of four modules 11 share a common heat exchanger andfan 20, which is mounted to the gantry or other framework for coolingthe group of modules 11.

For forming a Compton sensor, one or more modules 11 are used. Forexample, two or more modules 11 are positioned relative to a patient bedor imaging space to detect photon emissions from the patient. Anarrangement of a greater number of modules 11 may allow for detection ofa greater number of emissions. By using the wedge shape, modules 11 maybe positioned against, adjacent, and/or connected with each other toform an arc about the patient space. The arc may have any extent. Themodules 11 directly contact each other or contact through spacers or thegantry with small separation (e.g., 10 cm or less) between the modules11.

In one example, four modules 11 are positioned together, sharing a clockand/or synchronization bridge 18, one or more data bridges 17, and aheat exchanger and fan 20. One, two, or four fiber data links 16 areprovided for the group of modules 11. Multiple such groups of modules 11may be positioned apart or adjacent to each other for a same patientspace.

Due to the modular approach, any number of modules 11 may be used.Manufacturing is more efficient and costly by building multiple of thesame component despite use of any given module 11 in a differentarrangement than used for others of the modules 11.

The fiber data links 16 of the modules 11 or groups of modules 11connect to the Compton processor 19. The Compton processor 19 receivesthe values for the parameters for the different events. Using the energyand timing parameters, scatter and catcher events are paired. For eachpair, the spatial locations and energies of the pair of events are usedto find the angle of incidence of the photon on the scatter detector 12.The event pairs are limited to events in the same module 11 in oneembodiment. In another embodiment, catcher events from the same ordifferent modules 11 may be paired with scatter events from a givenmodule 11. More than one Compton processor 19 may be used, such as forpairing events from different parts of a partial ring 40.

Once paired events are linked, the Compton processor 19 or anotherprocessor may perform computed tomography to reconstruct a distributionin two or three dimensions of the detected emissions. The angle or lineof incidence for each event is used in the reconstruction.

FIGS. 4A-6 shows one example arrangement of modules 11. The modules 11form a ring 40 surrounding a patient space. FIG. 4A shows four suchrings 40 stacked axially. FIG. 4B shows the scatter detectors 12 andcorresponding catcher detectors 13 of the modules 11 in the ring 40.FIG. 4C shows a detail of a part of the ring 40. Three modules 11provide corresponding pairs of scatter and catcher detectors 12, 13.Other dimensions than shown may be used. Any number of modules 11 may beused to form the ring 40. The ring 40 completely surrounds the patientspace. Within a housing of a medical imaging system, the ring 40connects with a gantry 50 or another framework as shown in FIG. 5. Thering 40 may be positioned to allow a patient bed 60 to move a patientinto and/or through the ring 40. FIG. 6 shows an example of thisconfiguration.

The ring may be used for Compton-based imaging of emissions from apatient. FIG. 7 shows an example of using the same type of modules 11but in a different configuration. A partial ring 40 is formed. One ormore gaps 70 are provided in the ring 40. This may allow for othercomponents to be used in the gaps and/or to make a less costly system byusing fewer modules 11.

FIG. 8 shows another configuration of modules 11. The ring 40 is a fullring. Additional partial rings 80 are stacked axially relative to thebed 60 or patient space, extending the axial extent of detectedemissions. The partial rings 80 are in an every other or every group ofN modules 11 (e.g., N=4) distribution rather than the two gaps 70partial ring 40 of FIG. 7. The additional rings may be full rings. Thefull ring 40 may be a partial ring 80. The different rings 40 and/orpartial rings 80 are stacked axially with no or little (e.g., less than½ a module's 11 axial extent) apart. Wider spacing may be provided, suchas having a gap of more than one module's 11 axial extent.

FIG. 9 shows yet another configuration of modules 11. One module 11 or asingle group of modules 11 is positioned by the patient space or bed 60.Multiple spaced apart single modules 11 or groups (e.g., group of four)may be provided at different locations relative to the bed 60 and/orpatient space.

In any of the configurations, the modules 11 are held in position byattachment to a gantry, gantries, and/or other framework. The hold isreleasable, such as using bolts or screws. The desired number of modules11 are used to assemble the desired configuration for a given medicalimaging system. The gathered modules 11 are mounted in the medicalimaging system, defining or relative to the patient space. The result isa Compton sensor for imaging the patient.

The bed 60 may move the patient to scan different parts of the patientat different times. Alternatively or additionally, the gantry 50 movesthe modules 11 forming the Compton sensor. The gantry 50 translatesaxially along the patient space and/or rotates the Compton sensor aroundthe patient space (i.e., rotating about the long axis of the bed 60and/or patient). Other rotations and/or translations may be provided,such as rotating the modules 11 about an axis non-parallel to the longaxis of the bed 60 or patient. Combinations of different translationsand/or rotations may be provided.

The medical imaging system with the Compton sensor is used as a standalone imaging system. Compton sensing is used to measure distribution ofradiopharmaceutical in the patient. For example, the full ring 40,partial ring 40, and/or axially stacked rings 40, 80 are used as aCompton-based imaging system.

In other embodiments, the medical imaging system is a multi-modalityimaging system. The Compton sensor formed by the modules 11 is onemodality, and another modality is also provided. For example, the othermodality is a single photon emission computed tomography (SPECT), a PET,a CT, or a MR imaging system. The full ring 40, partial ring 40, axiallystacked rings 40,80, and/or singular module 11 or group of modules 11are combined with the sensors for the other type of medical imaging. TheCompton sensor may share a bed 60 with the other modality, such as beingpositioned along a long axis of the bed 60 where the bed positions thepatient in the Compton sensor in one direction and in the other modalityin the other direction.

The Compton sensor may share an outer housing with the other modality.For example, the full ring 40, partial ring 40, axially stacked rings40,80, and/or singular module 11 or group of modules 11 are arrangedwithin a same imaging system housing for the sensor or sensors of theother modality. The bed 60 positions the patient within the imagingsystem housing relative to the desired sensor. The Compton sensor may bepositioned adjacent to the other sensors axially and/or in a gap at asame axial location. In one embodiment, the partial ring 40 is used in acomputed tomography system. The gantry holding the x-ray source and thex-ray detector also holds the modules 11 of the partial ring 40. Thex-ray source is in one gap 70, and the detector is in another gap 70. Inanother embodiment, the single module 11 or a sparse distribution ofmodules 11 connects with a gantry of a SPECT system. The module 11 isplaced adjacent to the gamma camera, so the gantry of the gamma cameramoves the module 11. Alternatively, a collimator may be positionedbetween the modules 11 and the patient or between the scatter andcatcher detectors 12, 13, allowing the scatter and/or catcher detectors12, 13 of the modules 11 to be used for photoelectric event detectionfor SPECT imaging instead of or in addition to detection of Comptonevents.

The module-based segmentation of the Compton sensor allows the samedesign of modules 11 to be used in any different configurations. Thus, adifferent number of modules 11, module position, and/or configuration ofmodules 11 may be used for different medical imaging systems. Forexample, one arrangement is provided for use with one type of CT systemand a different arrangement (e.g., number and/or position of modules 11)is used for a different type of CT system.

The module-based segmentation of the Compton sensor allows for moreefficient and costly servicing. Rather than replacing an entire Comptonsensor, any module 11 may be disconnected and fixed or replaced. Themodules 11 are individually connectable and disconnectable from eachother and/or the gantry 50. Any bridges are removed, and then the module11 is removed from the medical imaging system while the other modules 11remain. It is cheaper to replace an individual module 11. The amount oftime to service may be reduced. Individual components of a defectivemodule 11 may be easily replaced, such as replacing a scatter or catcherdetector 12, 13 while leaving the other. The modules 11 may beconfigured for operation with different radioisotopes (i.e., differentenergies) by using corresponding detectors 12, 13.

FIGS. 11-15 show embodiments where the modules 11 selectably include aphysical aperture for SPECT detection using the photoelectric effect.The modules may selectably include a scatter detector for Comptondetection. The modules may be used for both Compton detection andphotoelectric detection. A multi-modality medical imaging system isformed from one or more of the modules. The arrangements and componentsof the modules 11 discussed for FIGS. 1-9 may be used for the modules 11with the physical aperture.

The segmented detection modules 11 may be used to form a geodesicdome-like multi-layer multi-modal camera. The camera is segmented intomodules that house the detection units. Each module 11 is independent,and when assembled into a ring, partial ring or other configuration, themodules 11 may communicate with each other. Each module 11 includes aninner shell-like layer, denominated scatter layer, and an outershell-like layer, denominated catcher layer. Where multiple modulus 11are used, the modules may at least partly surround the imaging object.

FIG. 16 shows an embodiment of a medical imaging system where themodules 11 do not include the scatter detector, so provides for modularcreation of a SPECT camera using the physical aperture and a detector.FIG. 15 shows an embodiment of a medical imaging system where themodules 11 include the scatter detector, so provides for modularcreation of a Compton camera using the scatter detector. The modules 11of FIG. 15 may include the physical aperture, so operate both as aCompton camera and a SPECT camera. Depending on the desired energies tobe imaged for any given system, the base module with the catcherdetector may be fitted with either or both of the scatter detector(e.g., higher energies) or the physical apertures (e.g., lowerenergies).

FIG. 11 illustrates the detector structure of one module 11 where boththe physical aperture 110 and the scatter detector 12 are selected andincluded in the same module 11. The module 11 includes the scatterdetector 12 and the catcher detector 13. The scatter detector 12 and/orcatcher detector 13 are solid-state detectors, so the module 11 is asolid-state detector module. A bracket, frame, clips, or othermechanical structure is provided for positioning the scatter detector 12within the module 11 where the scatter detector 12 is selected to beincluded. The position may be at a given distance from the catcherdetector 13 or may be adjustable in assembly or after assembled.Mechanical structures may be provided for positions of additionalcatcher and/or scatter detectors in the module 11 so that the designerof a given imaging system may select the number of catcher and/orscatter layers to include.

Additional catcher or scatter detectors 12, 13 may be provided, such aslayering detectors 12, 13 in parallel normal to a radial from thepatient space (e.g., along the axis of rotation in FIG. 11). Anyemissions passing through one catcher detector 13 may interact inanother catcher detector 13. Similarly, the intermediate detectors mayoperate as scatter detectors 12 due to an emission passing through theinitial scatter detector 12. The intermediate detectors may have a samestructure as either the scatter detector 12 or the catcher detector 13,but operate as scatter and/or catcher detectors 12, 13. One of thescatter detectors 12 generates Compton-scattering photons, which arecaptured by one of the sub-sequent catcher layers 13.

The modules 11 are independent yet may be assembled into a unit thatproduces multi-modal-based image formation images. The modules 11 allowfor the design freedom in the shape to change radius for each radialdetection unit, angular span of one module 11, and/or axial span. Thedimensions and position of the modules 11 relative to a patient spacemay be altered in design as needed, such as by using a differenthousing.

Any of the shapes described for FIGS. 1-9 may be used. For example, FIG.1 shows modules 11 with four sides in cross section orthogonal to aradial from the patient space. In one embodiment, the modules 11 havethree, five, six, or more sides in cross section orthogonal to a radialfrom the patient space. FIG. 11 shows a six sided module 11. Wheremultiple modules 11 are to be used together, all the modules have a samenumber of sides. Alternatively, different modules 11 with a differentnumber of sides are used together, such as a combination of modules 11with five and six sides.

The three, five, or six sided modules have a narrower orthogonal crosssection closer to the patient space than the orthogonal cross sectionfurther from the patient space, allowing for a geodesic dome. Themodules 11 may be positioned to form a sphere or geodesic dome. For anygiven imaging system, a full dome is not used. Two or more modules 11may be positioned to form part of a geodesic dome. In alternativeembodiments, the modules 11 are not shaped for forming a sphere orgeodesic dome, such as the modules 11 of FIG. 1 being shaped to form aring or cylinder.

The modules 11 are cylindrically symmetric. A narrowest end of each ofthe modules 11 is closest to a patient space of the medical imagingsystem. A widest end of each of the modules 11 is further or furthestfrom the patient space. The scatter detector 12 is narrower and has lessarea than the catcher detector 13.

Where the modules 11 include both a scatter and catcher detectors 12,13, Compton-based imaging may be provided. To detect events using thephotoelectric effect for SPECT, a physical aperture 110 is included inthe module 11. The physical aperture 110 is a plate or sheet ofmaterial. The physical aperture 110 is of any material that is opaque tolower energy (e.g., at about or less than 140.5 keV), such as lead ortungsten. Any thickness may be used, such as 0.5-5 mm (e.g., 1-3 mm).The thickness is chosen to allow all or some higher energy emissions orphotons (e.g., >>140.5 keV) to pass for Compton detection.

The physical aperture 110 is positioned between the position for thescatter detector 12 and the catcher detector 13. Where intermediatedetectors are provided, the physical aperture 110 may be between any ofthe detector layers. The coded aperture may be adjacent to the catcherdetector 13, such as within 1 cm (e.g., within 5 mm), or spaced furtherfrom the catcher detector 13. In alternative embodiments, the physicalaperture 110 is positioned in front of (i.e., closer to the patientspace) of the position for the scatter detector 12.

A bracket, frame, clips, or other mechanical structure is provided forpositioning the physical aperture 110 within the module 11 where thephysical aperture 110 is selected to be included. The position may be ata given distance from the catcher detector 13 or may be adjustable inassembly or after assembled.

The physical aperture 110 is orthogonal to the radial form the patientspace, so is parallel with the detectors 12, 13. Alternatively, thephysical aperture 110 is not parallel with one or both detectors 12, 13and/or is not orthogonal to the radial from the patient space. Theradial is shown in FIG. 11 as an axis of rotation.

The physical aperture 110 has a same shape as the detectors 12, 13. Forexample and as shown in FIG. 11, the physical aperture 110 and detectors12, 13 are six sided. The physical aperture 110 may have a differentouter circumference shape than one or both detectors 12, 13.

The physical aperture 110 is a coded aperture. Holes in a regular orvarying pattern are provided to cast a shadow on the catcher detector13. The holes are of the same or different shapes and/or sizes. Theholes are of sufficient size that emissions from different angles (e.g.,0-40 degrees away from orthogonal to the physical aperture 11) may passthrough a hole. The coding in the holes of the aperture causeoverlapping shadows on the catcher detector 13 as illuminated from asource (e.g., patient). The coding of the shadows may be used as a maskin reconstruction to deconvolve an image. In alternative embodiments,the physical aperture 110 is a parallel hole collimator (e.g., onlyemissions 0-1 degree from orthogonal pass through a hole).

To reduce noise, source size, and/or scattering problems, the codedaperture may be a time-encoded aperture. The physical aperture 110rotates about a center axis (e.g., radial from the patient space). Thecoding in the shadow is shifted or changed for detecting at differenttimes. Detections from different positions of the coded aperture 110relative to the catcher detector 13 are used to reduce noise and/ordistinguish background emissions from emissions from the patient. Thetime-encoded coded-aperture near the catcher detector 13 rotates aroundthe axis of rotation to improve image quality and increase the field ofview. In other embodiments, the physical aperture 110 translates insteador in addition to rotating. The translation shifts the position of thephysical aperture 110 relative to the catcher detector 13 within themodule 11. Other time encoding may be used.

In one embodiment, the physical aperture 110 is positioned relative tothe catcher detector to cast the shadow on a center region 112 of thecatcher detector 13 and not an outer region 114 of the catcher detector13. For example, the physical aperture 110 has a same or similar (e.g.,within 10%) area as the scatter detector 12 and a lesser area than thecatcher detector 13. Due to scattering in Compton detection, the photonsdetected by the catcher layer for the Compton effect are more likely tobe away from the center of the catcher detector 13. Conversely, sincescattering is not used for the photoelectric effect, the photonsdetected using the photoelectric effect are more likely to be in thecenter region 112. The center region 112 records Compton scatteredphotons as well as photoelectric events that do not interact with innerdetectors. The outer region 114 records only or mostly Compton scatteredevents from inner scatter detector 12 or other scatter detectors 12.

The actual structure of the catcher detector 13 may be uniform or thesame for both the central region 112 and the outer region 114, but mayhave different pixel size, thickness, and/or other characteristics forthe different regions 112, 114. The readings from the catcher detector13 may be limited to one or both regions 112, 114 based on the type ofimaging performed. Alternatively, different structure is used, ordetection over the entire catcher detector 13 is used regardless of thetype of imaging. Where modules 11 are arranged to communicate, Comptonevents from one module 11 may be detected with either region 112, 114 ofanother module 11.

The image processor 19 is configured to detect emissions with aphotoelectric effect using the physical aperture 110 and the catcherdetector 13 and to detect emissions with a Compton effect using thescatter detector 12 and the catcher detector 13. The detected eventsoutput by the circuit boards 14 are used by the image processor 19 forSPECT or Compton imaging. For SPECT, the coded or time-encoded apertureis used without events from the scatter detector 12. Photons at energiesat about 140.5 keV or less are detected using the photoelectric effect.For Compton scatter, the scatter detector 12 and catcher detector 13 areused without the shadowing form the physical aperture 110. Photons atenergies an order of magnitude larger (e.g., 1450 keV or larger) aredetected using the Compton effect. The same modules 11 and imageprocessor 19 are used for both photoelectric and Compton imaging.

For Compton detection, the events from the scatter and catcher detectors12, 13 are paired and used to determine angles of incidence for Comptonevents in one or more modules 11. Photons may interact first in thescatter-layer(s) by Compton-scatter and then in the catcher-layer byphotoelectric effect. These photons trigger both the scatter-layer(s)and the catcher-layer and deposit their full energy on all layers(multi-layer event). Due to scattering, over half or most of the eventsdetected in the catcher detector 13 are in the outer region 114. Thephoton interaction events are primarily (over half or most) detected inthe outer region 114. Compton reconstruction is used to determine thecorrect source direction by knowing (estimating) the Compton kinematicsbased on measured position (x,y,z) and energy (E) for paired events.

For photoelectric detection (i.e., SPECT imaging), photoelectric eventsfrom the catcher detector 13 are counted. The physical apertures 110 andcatcher detectors 13 of the modules 11 are used. Photons may interactonly in the catcher-layer by the photoelectric effect. The low energyphotons may not trigger the scatter-layer and instead deposit their fullenergy on the catcher-layer (single-layer event). Since scattering isnot used, the photoelectric events are counted from the center region112 and not the outer region 114 of the catcher detector 13. Events fromthe outer region 114 may be used as measures of background.

A time-encoded coded-aperture may rotate around the axis of the module11 and is used to determine the correct source direction. Thetime-encoded coded-aperture may reduce background (e.g., scatter, higherenergy photons emitted by the source, etc.).

The image processor 19 is configured to generate a SPECT image. Thecounts and the positions on the catcher detector 13 (i.e., positionsindicating the lines of response) are used to reconstruct a two orthree-dimensional representation of the patient. The locations ofemissions are represented. The image processor 19 is configured togenerate a Compton image from the Compton events. A two orthree-dimensional representation is reconstructed from the Comptonscatter events and the corresponding estimated angles. For athree-dimensional representation of the object or image space, atwo-dimensional image may be three-dimensionally rendered from therepresentation.

The display 22 is a CRT, LCD, projector, printer, or other display. Thedisplay 22 is configured to display the SPECT image and/or the Comptonimage. The image or images are stored in a display plane buffer and readout to the display 22. The images may be displayed separately or arecombined, such as displaying the Compton image overlaid with or adjacentto the SPECT image.

FIGS. 12-16 show medical imaging systems formed from two or more modules11. The shape of the solid-state detector modules 11 allow the modules11 to stack together with or without direct contact to form part of ageodesic dome. The modules 11 may be combined to form a 3D geodesicdome-like SPECT-Compton camera. FIGS. 12-16 show different realizationsof the same concept having 18, 34, 54, 3 and 3, modules respectively.

FIG. 12 shows the modules 11 used to form a full ring 120. Based on theradius of the ring and size of the modules 11, eighteen modules 11 formthe full ring 120. More or fewer modules 11 may be used to form the fullring 120. One or more partial rings may be formed instead.

FIG. 13 shows the modules 11 used to form two full rings 130, 132. Thetwo rings 130, 132 intersect, so share two of the modules 134. One ofthe rings 130 is at 90 degrees to the other ring 132. Depending on thenumber of sides and/or the shape of the modules 134, other angles may beprovided. In the example of FIG. 13, thirty-four modules 11 form the tworings 130, 132. Other numbers of modules 11 may be used. One or bothrings 130, 132 may be partial rings. The rings 130, 132 are separate butintersect. In other embodiments, the rings 130, 132 do not intersect andare spaced from each other in parallel or non-parallel planes.Additional rings may be included.

The rings 130, 132 are held in place or stationary. In otherembodiments, the rings 130, 132 connect to hinges or a rotary axis. Therings 130, 132 pivot about a common axis, such as an axis through thetwo shared modules 134. Translation and/or rotation of both rings 130,132 or each ring 130, 132 independently may be provided.

FIG. 14 shows the modules 11 used to form three rings into a larger partof a geodesic dome 140 as compared to FIGS. 12 and 13. Part of aspherical shell is formed from the segmented modules 11. The three ringsare axially adjacent to each other with little (e.g., less than ½ widthof a module 11) or no separation. The rings may be in direct contactwith each other and/or mounted to a same gantry or framework. Three fullrings are shown, but one or more rings may be partial rings. Two, four,or more rings may be used. In the example of FIG. 14, fifty-four modules11 are used for the three rings, but additional or fewer number ofmodules 11 may be used.

FIG. 15 shows three modules 11 positioned relative to the patient bed60. One, two, four, or more modules 11 may be used. The modules 11 arespaced from each other by one or more module widths, but lesserseparation or adjacent placement may be used. The modules 11 may beconnected with another modality, such as a dedicated SPECT camera. Themodules 11 connect with a gantry to allow rotation around and/ortranslation (e.g., transaxially) along a patient. Alternatively oradditionally, the bed 60 moves the patient relative to the modules 11.

FIG. 16 shows the three-module arrangement of FIG. 15 using a differenttype of module 160. The scatter detector 12 is removed, allowing themodules 160 to be less high or have a smaller extent along the radialfrom the patient space. The same height may be used, such as using thesame housings but without the scatter detector 12. Compton imaging isnot provided, so the modules 160 use the physical aperture 110 with oneor more catcher detectors 13. The catcher detector 13 functions with thetime encoded coded aperture 110 for SPECT or photoelectric effect-basedimaging. The catcher detector 13 absorbs photons by the photoelectriceffect. The time encoded coded-aperture 110 near the catcher layer mayrotate around the axis of rotation to improve image quality. The codedaperture may also move in the XY detector plane (sideways) to increasethe field of view. Other arrangements of the modules 160 for SPECTimaging may be used, such as the arrangements of FIGS. 12-14. A singlemodule 160 may be used. Less or more modules built in any of differentconfigurations may be used.

FIG. 10 shows one embodiment of a flow chart of a method for forming,using, and repairing a camera selectable to be a Compton camera, a SPECTcamera, or both. The camera is formed in a segmented approach. Ratherthan hand assembling the entire camera in place, one or more catcherdetectors are positioned relative to each other to form a desiredconfiguration of the camera. The catcher detectors are arranged to beusable for relatively lower emission energies with a coded aperture andto be usable for relatively higher emission energies with a scatterdetector. This selectable and segmented approach may allow differentconfigurations using the same parts, ease of assembly, ease of repair,and/or integration with other imaging modalities.

Other embodiments form a combination of a Compton camera and a SPECTcamera where both the scatter detector and coded apertures are selectedto be used in a same camera with the catcher detector. The segmentedmodule 11 of FIG. 11 is used. The modules 160 of FIG. 16 may be used forforming a SPECT camera without the scatter detector being included. Themodules 11 of FIG. 11 may be used for forming a Compton camera withoutthe coded apertures.

The method may be implemented by the system of FIG. 1 to assemble aCompton sensor as shown in any of FIGS. 4-9. The method may beimplemented by the system of FIG. 11 to assemble a Compton sensor asshown in any of FIGS. 12-16. Other systems, modules, and/or configuredCompton sensors may be used.

The acts are performed in the order shown (i.e., top to bottom ornumerically) or other orders. For example, act 108 may be performed aspart of act 104.

Additional, different, or fewer acts may be provided. For example, acts102 and 104 are provided for assembling the Compton camera withoutperforming acts 106 and 108. As another example, act 106 is performedwithout other acts.

In act 102, catcher detectors are housed in separate housings. Modulesare assembled where each module includes a catcher detector. A machineand/or person manufactures the housings. Only one housing andcorresponding module may be used.

The modules are shaped to abut where the scatter and catcher detectorpairs of different ones of the housings are non-planar. For example, awedge shape and/or positioning is provided so that the detector pairsfrom an arc, such as shown in FIG. 4C. The shape allows and/or forcesthe arc shape when the modules are positioned against one another.

For the Compton-SPECT camera (e.g., FIG. 11), the scatter detector,coded aperture, and catcher detector are housed in a housing. Thehousings and corresponding modules have any shape, such as being shapedto be part of or form part of a geodesic dome. The housing selectablyincludes one or both of the scatter detector and the coded aperture.Depending on the design and/or emission energy requirements, the samehousing with positions for both the scatter detector and the codedaperture may be used even where only one of the scatter detector orcoded aperture are positioned or installed. Alternatively, differenthousings are used depending on which of the scatter detector and/orcoded aperture are to be included.

In act 104, the housings are abutted. A person or machine assembles theCompton sensor from the housings. By stacking the housings adjacent toeach other with direct contact or contact through spacers, gantry, orframework, the abutted housings form the arc. A full ring or partialring is formed around and at least in part defines a patient space.Based on the design of the Compton camera, SPECT camera, orCompton-SPECT camera, any number of housings with the correspondingscatter and catcher detector pairs are positioned together to form acamera. A single housing may be used.

The housings may be abutted as part of a multi-modality system or tocreate a single imaging system. For a multi-modality system, thehousings are positioned in a same outer housing and/or relative to asame bed as the sensors for the other modality, such as SPECT, PET, CT,or MR imaging system. The same or different gantry or support frameworkmay be used for the housings of the Compton camera and the sensors forthe other modality. For the embodiments of FIGS. 11-15, the modulesprovide the multi-modality by providing for both a Compton camera andthe SPECT imaging system.

The configuration or design of the Compton camera defines the numberand/or position of the housings. Once abutted, the housings may beconnected for communications, such as through one or more bridges. Thehousings may be connected with other components, such as an air coolingsystem and/or a Compton processor.

In act 106, the assembled Compton camera detects emissions. A givenemitted photon interacts with the scatter detector. The result isscattering of another photon at a particular angle from the line ofincidence of the emitted photon. This secondary photon has a lesserenergy. The secondary photon is detected by the catcher detector. Basedon the energy and timing of both the detected scatter event and catcherevent, the events are paired. The positions and energies for the pairedevents provides a line between the detectors and an angle of scattering.As a result, the line of incidence of the emitted photon is determined.

To increase the likelihood of detecting the secondary photon, thecatcher events from one housing may be paired with the scatter events ofanother housing. Due to the angles, scatter from one scatter detectormay be incident on the paired catcher detector in the same housing or acatcher detector in another housing. By the housings being open in thedetector region and/or using low photon attenuating materials, a greaternumber of Compton events may be detected.

The detected events are counted or collected. The lines of response orlines along which the different Compton events occur are used inreconstruction. The distribution in three dimensions of the emissionsfrom the patient may be reconstructed based on the Compton sensing. Thereconstruction does not need a collimator as the Compton sensingaccounts for or provides the angle in incidence of the emitted photon.

Using the Compton-SPECT modules 11 of FIG. 11, the modules may also beused to detect emissions as photoelectric events. The lower energyemissions pass through the scatter detector. These emissions may passthrough holes in the coded aperture or are blocked by the codedaperture. The catcher detector detects at least some of the emissionspassing through the holes of the coded aperture. Depending on theselection to include either or both of the scatter detector and codedaperture, emissions at relatively lower and/or higher energies aredetected.

The detected events are used to reconstruct the locations of theradioisotope. Compton and/or photoelectric images are generated from thedetected events and corresponding line information from the events.

In act 108, a person or machine (e.g., robot) removes one of thehousings. When one of the detectors or associated electronics of ahousing fails or is to be replaced for detecting at different energies,the housing may be removed. The other housings are left in the medicalimaging system. This allows for easier repair and/or replacement of thehousing and/or detectors without the cost of a greater disassemblyand/or replacement of the entire Compton camera.

While the invention has been described above by reference to variousembodiments, it should be understood that many changes and modificationscan be made without departing from the scope of the invention. It istherefore intended that the foregoing detailed description be regardedas illustrative rather than limiting, and that it be understood that itis the following claims, including all equivalents, that are intended todefine the spirit and scope of this invention.

I/We claim:
 1. A multi-modality medical imaging system comprising: afirst module having a first catcher detector; and an image processorconfigured to determine angles of incidence for Compton events where afirst scatter detector is included in the first module and to countphotoelectric events where a first physical aperture is included in thefirst module.
 2. The multi-modality medical imaging system of claim 1wherein the first physical aperture comprises a coded aperture of leador tungsten.
 3. The multi-modality medical imaging system of claim 2wherein the coded aperture comprises a time-encoded aperture rotatableabout an axis and/or translatable in a plane perpendicular to the axisto cast shadows with different positions on the first catcher detector.4. The multi-modality medical imaging system of claim 1 wherein thefirst physical aperture and the first catcher detector are parallel, thefirst physical aperture having a shadow on the first catcher detector ina center region of the first catcher detector and not an outer region ofthe first catcher detector, and wherein the image processor isconfigured to count the photoelectric events from the center region andnot the outer region and to determine the angles of incidence for theCompton events with photon interaction events primarily from the outerregion.
 5. The multi-modality medical imaging system of claim 1 furthercomprising a second module having a second catcher detector; and whereinthe first and second modules are three, five, or six sided incross-section orthogonal to a radial from a patient space.
 6. Themulti-modality medical imaging system of claim 5 wherein the first andsecond modules are cylindrically symmetric, a narrowest end of each ofthe first and second modules being closest to a patient space of themedical imaging system, a widest end of each of the first and secondmodules being furthest from the patient space.
 7. The multi-modalitymedical imaging system of claim 1 wherein the first module furthercomprises circuit boards orthogonal to the first catcher detector,application specific integrated circuits with the first catcherdetector, flexible circuits connecting the application specificintegrated circuits to the circuit boards, and positions for one or moreadditional catcher and/or scatter layers between the first catcher layerand the first scatter layer.
 8. The multi-modality medical imagingsystem of claim 1 wherein the first module is part of a ring or partialring around a patient space of the medical imaging system.
 9. Themulti-modality medical imaging system of claim 8 further comprisingadditional modules for the ring or partial ring and for another ring orpartial ring intersecting with the ring or partial ring at two of theadditional modules.
 10. The multi-modality medical imaging system ofclaim 9 wherein the ring or partial ring and the other ring or partialring are 90 degrees apart.
 11. The multi-modality medical imaging systemof claim 8 further comprising an additional ring or partial ring ofmodules axially adjacent to the ring or partial ring with the firstmodule, the additional ring or partial ring and the ring or partial ringforming part of a geodesic dome.
 12. The multi-modality medical imagingsystem of claim 1 wherein the image processor is configured to generatea single photon emission computed tomography image from the count and aCompton image from the Compton events, and further comprising a displayconfigured to display the single photon emission computed tomographyimage and the Compton image.
 13. The multi-modality medical imagingsystem of claim 1 wherein the first scatter detector is included in thefirst module at a position for the first scatter detector whererelatively higher energies are to be detected and wherein the firstphysical aperture is included in the first module at a position for thefirst physical aperture where relatively lower energies are to bedetected.
 14. A medical imaging system comprising: solid-state detectormodules each with a first detector arranged to be used with either orboth of a plate forming a coded aperture and a scatter detector; thesolid-state detector modules each having a width that is lesser closerto a patient space than further from the patient space such that thesolid-state detector modules stack together in at least a partial ringabout the patient space.
 15. The medical imaging system of claim 14wherein each of the solid-state detector modules further comprises thescatter detector and the plate, the plate being between the scatterdetector and the first detector, further comprising an image processorconfigured to detect emissions with a photoelectric effect using theplate and the first detector and to detect emissions with a Comptoneffect using the scatter detector and the first detector.
 16. Themedical imaging system of claim 14 wherein each of the solid-statedetector modules includes the plate, the plate being rotatable and/ortranslatable relative to the first detectors within the respectivesolid-state detector modules.
 17. The medical imaging system of claim 14wherein the solid-state detector modules stack to form the at leastpartial ring as two separate rings sharing two of the solid-statemodules.
 18. A method for forming a Compton camera and/or a singlephoton emission computed tomography camera, the method comprising:housing a catcher detector in a housing, the catcher detector arrangedto be usable for relatively lower emission energies with a physicalaperture and to be usable for relatively higher emission energies with ascatter detector, the housing shaped for stacking around a patient spacewith other housings; and mounting the housing relative to a patient bedwith a selected one or both of the physical aperture and the scatterdetector.
 19. The method of claim 18 wherein mounting comprises forminga ring or partial ring with the housing and the other housings as partof a multi-modality system including the Compton camera using thescatter detector in the housing and a single photon emission computedtomography imaging system using the physical aperture in the housing.20. The method of claim 18 further comprising: detecting a firstemission as a Compton event with the scatter detector and the catcherdetector; and detecting a second emission as a photoelectric eventpassing through the physical aperture with the catcher detector.